PEI/Zr4+-coated Nanopore for Selective and Sensitive...
Transcript of PEI/Zr4+-coated Nanopore for Selective and Sensitive...
PEI/Zr4+
-coated Nanopore for Selective and Sensitive Detection of 1
ATP in Combination with Single-Walled Carbon Nanotubes 2
Siqi Zhang a,b
, Amin Bao b, Ting Sun
a*, Erkang Wang
b*, Jiahai Wang
a,b* 3
a College of Science, Northeastern University, Shenyang, 110819, China 4
b State Key Laboratory of Electroanalytical Chemistry, Changchun Institute of Applied 5
Chemistry, Chinese Academy of Science, Changchun, Jilin, 130022, China 6
*Corresponding author 7
E-mail: [email protected]; [email protected]; [email protected]; 8
Tel.: +86-0431-85262334; 9
Homepage: http://nanopore.weebly.com 10
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Abstract 1
By virtue of a biomimetic nanopore and single-walled carbon nanotubes, a new sensor for 2
adenosine triphosphate (ATP) detection is designed. As compared to the routine approach, the 3
present scenario does not entail the surface modification of nanopore with analyte-specific 4
probes. The underlying mechanism relies on a symmetric nanopore sequentially modified 5
with polyethyleneimine (PEI) and Zr4+
that can quantitate the concentration of ATP-bound 6
aptamer, while other free aptamers are removed by single-walled carbon nanotube (SWNTs). 7
The detection limit of the nanopore sensor is 27.46 nM, and the linear range is from 50 nM to 8
400 nM. The biosensor with an excellent selectivity against guanosine triphosphate (GTP), 9
uridine triphosphate (UTP), and cytosine triphosphate (CTP) can be applied in the real 10
samples such as Hela cell. 11
Keywords: nanopore, polyethyleneimine, Zr4+
, aptamer, ATP detection, single-walled carbon 12
nanotubes 13
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1. Introduction 15
In recent years, synthetic nanopores have intrigued scientists in different fields for their 16
easy preparation and functionalization (Ali et al. 2010; Liu et al. 2012). In terms of the 17
bioanalytical applications based on artificial nanopores, many excellent works have emerged. 18
Two approaches to accomplish the analysis of the target of interest are Resistive-Pulse 19
Sensing (RPS) (Sexton et al. 2010) and Ion-Current Rectification (ICR) (Fan et al. 2013; 20
Momotenko and Girault 2011), respectively. For nanopore in thin membrane and engineered 21
protein nanopore, Resistive-Pulse Sensing is an exclusive choice (Sexton et al. 2007). With 22
respect to the asymmetric nanopore in thick polymer membranes such as polyethylene 1
terephthalate (PET) and polycarbonate (PC) membranes (Yang et al. 2013), both approaches 2
can be used. However, Ion Current Rectification (Gao et al. 2014; Guo et al. 2011b) is much 3
more preferable than Resistive-Pulse Sensing. Firstly, the ion current rectification ratio 4
exhibited by the asymmetric nanopore is highly adjustable, which shows large value even 5
though the tip diameter is up to 50 nm (Wang and Martin 2008). Secondly, the surface area 6
around the nanopore tip plays a very crucial role in the molecular recognition, which increases 7
the capturing efficiency. On the contrary, this feature could degrade the detection efficiency of 8
the sensor based on RPS, since the target could be irreversibly bound to the nanopore surface 9
without dissociation from the surface due to the multivalent binding affinity. In 2008, Wang et 10
al. applied ICR in analysis of positively hydrophobic drugs with conically shaped nanopore in 11
kapton membrane(Wang and Martin 2008). Then other possible applications of the artificial 12
nanopores such as the detection of single molecules (Gao et al. 2014; Wang and Martin 2008; 13
Wen et al. 2013), protein(Ali et al. 2011a; Ali et al. 2013; Ali et al. 2010; Ali et al. 2011b), 14
DNA (Fu et al. 2009), metal ion(Han et al. 2013; Tian et al. 2013) and biomoleculars (Liu et 15
al. 2013; Tian et al. 2010; Zhang et al. 2013) were achieved. 16
Several factors, including buffer solution, pore size, pore geometry and charge density, 17
can be exploited to modulate the ion current rectification ratio for asymmetric nanopore. For 18
sensing applications, adjusting the surface charge is the most effective way to construct a 19
nanopore-based sensor. In order to make the nanopore sensor highly sensitive and selective, 20
functionalization of the nanopore surface is the most commonly used method. As compared 21
with those robust analytical techniques (Gao et al. 2011; Lin et al. 2011; Lu et al. 2013; Pu et 22
al. 2012; Song et al. 2014; Wang et al. 2007b; Wang et al. 2012; Zhang et al. 2010; Zhou et al. 1
2012), the sensitivity and selectivity are far less satisfactory. The obstacle is lack of an 2
efficient way to design the nanopore surface. The ideal sensor platform based on cone-shaped 3
nanopore must feature the property that low concentration of target can reverse the surface 4
charge status significantly after target interacts with the probe-immobilized nanopore surface. 5
But unfortunately, it is not easy to find a probe whose net charge is opposite to the target of 6
interest. Furthermore, probe immobilization brings high steric hindrance and also changes the 7
hydrophobicity of the nanopore, which is not favorable for target binding. 8
In the present study, a new paradigm based on cone-shaped nanopore combined with 9
SWNTs is proposed. The nanopore coated with Zr4+
acts as a counter which can quantitatively 10
detect the concentration of folded DNA (or aptamer); at the same time, SWNTs can remove 11
the excess single-stranded DNA (ssDNA) (or aptamer) which has not folded into duplex 12
conformation the presence of target (Guo et al. 2010; Guo et al. 2011a; Zhang et al. 2010). 13
Zirconium ion (Zr4+
) which has strong affinity with the phosphate containing groups, is 14
considered as an ideal candidate for immobilization or detection of biomolecules with 15
phosphate groups (Shervedani and Pourbeyram 2009). Similar studies have demonstrated the 16
adsorption of DNA via phosphate groups (Fang et al. 2011; Liu et al. 2004; Wang et al. 2007b) 17
or the immobilization of laccase via enzyme carboxylate terminal groups onto the solid 18
surface modified by Zr4+
(Fang et al. 2008; Fang et al. 2011; Meng et al. 2012; Qi et al. 2013).
19
By taking ATP detection as an incarnation of this new paradigm, a new sensor for ATP 20
detection is constructed as illustrated in Scheme 1. The presence of ATP induces the folding 21
ATP aptamer into a compact structure with the formation of aptamer-ATP complexes (Wang et 22
al. 2007b). The SWNTss could facilely remove the unbound aptamer instead of the compact 1
complex. The compactly folded structure has much weaker adsorption propensity than the 2
free aptamer.(Song et al. 2014; Wang et al. 2012). Instead, the aptamer-ATP complexes can be 3
easily accumulated on the nanopore surface via the Zr4+
-PO43-
interaction. Before the DNA 4
adsorption, the nanopore coated with Zr4+
-PEI is positively charged. Whereas negatively 5
charged DNA can neutralize the surface charge of the nanopore, leading to the change of 6
current through nanopore which can be monitored by I-V curves. Therefore, the concentration 7
of ATP could be indirectly quantitated and this sensor is also demonstrated to be selective 8
toward ATP instead of other ATP analogues such as UTP, CTP, and GTP). 9
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2. Experimental 11
2.1. Chemicals and materials 12
12 µm thick polyethylene terephthalate (PET) which was irradiated with swift Au ion of 13
11.4 GeV/nucleon at UNILAC linear accelerator to create a single damage track through the 14
membrane were obtained from GSI, Darmstadt, Germany. Potassium chloride (KCl), sodium 15
hydroxide (NaOH) were purchased from Beijing Chemical Reagent Company (Beijing, 16
China). Single-walled carbon nanotubes were purchased from Chengdu Organic Chemicals 17
Co. Ltd. (Chengdu, China). The surfactant DOW fax 2A1 was obtained from DOW Chemical. 18
Tris and zirconium acetate was purchased from aladdin reagent. Polyethyleneimine 19
(Mw=25000, branched PEI), adenosine triphosphate (ATP), guanosine triphosphate (GTP), 20
cytidine triphosphate (CTP) and uridine triphosphate (UTP) were purchased from Sigma–21
Aldrich. Ultrapage purified oligonucleotides were obtained from Sangon Biotechnology Co., 22
Ltd. (Shanghai, China). ATP binding aptamer 5’-ACCT GGGG GAGT ATTG CGGA GGAA 1
GGT-3’. The FAM-labeled ATP aptamer 5’-ACCT GGGG GAGT ATTG CGGA GGAA GGT- 2
FAM-3’. Oligonucleotides were stored at -20 oC and were heated to 95
oC for 5 min and 3
gradually cooled to room temperature before use. 4
2.2 Nanopore preparation 5
Single conical nanopore was prepared in 12 µm thick polyethylene terephthalate (PET) 6
membrane by the track-etching technique. Either side of the tracked PET membrane was 7
independently exposed to the UV light (365 nm and 254 nm) for 1 h, and then the membrane 8
was embedded between two chambers of a conductivity cell so that different electrolyte 9
solution could be placed on each side of the PET membrane. The procedure of chemical 10
etching included two steps. An etching solution (6 M NaOH) was placed on one side of the 11
membrane and a protecting solution which neutralized the etchant (1 M HCOOH and 0.7% 12
2A1) was placed on the other at 40 oC for 1.5 h in the first etching step. Each side of 13
conductivity cell was added with a Pt wire. A Keithley 2536A picoammeter/voltage-source 14
(Keithley Instruments, Cleveland, OH) was employed to measure the ion current while 15
chemical etching using a transmembrane potential of 1 V. In the second step, the membrane 16
was placed in the centrifuge tube containing 2 M NaOH for 5 min at 65 o
C. The same 17
operating procedure was applied to the multi-tracked PET membranes ( 1×106 tracks cm
-2). 18
The tip diameter of the different nanopores was 74 nm, 82 nm, 78 nm, 92nm according to the 19
formula (Figure S2) respectively, while base diameter of the nanopore was 1100 nm (Figure 20
S1). 21
2.3 Chemical modification of the nanopore 22
Polyethyleneimine was immobilized onto the PET surface through electrostatic adsorption. 1
Then an aqueous solution of polyethyleneimine (PEI, 1% wt) was placed on both sides of the 2
track-etched membrane for 5 h. After polyethyleneimine was immobilized onto the membrane, 3
an aqueous solution of zirconium acetate (8% wt) was placed on the tip side of the conical 4
nanopore for 30 min. All the reactions were conducted at 25 oC. 5
2.4 Field-emission scanning electron microscopy and XPS characterization 6
The field-emission scanning electron microscopy (ESEM XL-30) was utilized to image 7
the morphology of the nanopores. Multi-tracked PET membranes (1×106 tracks cm
-2 ) was 8
prepared as described in the Experiment 2.2. The images of tip and base side of the nanopore 9
were shown in the Figure S1 (supporting information). 10
X-ray photoelectron spectroscopy (XPS) was used to characterize the surface chemistry 11
of the multi-tracked PET membranes. XPS data were obtained with an ESCALab250i-XL 12
electron spectrometer from VG Scientific using 300 W Al Kα radiations. 13
2.5 Current-versus-voltage measurements of nanopore 14
Ion current was measured by Keithley 2536A picoammeter/voltage-source (Keithley 15
Instruments, Cleveland, OH). The membrane was embedded in a two chambers of a 16
conductivity cell filled with Tris-HCl buffer solution (pH=7.4, 100 mM KCl 10mM Tris). 17
Ag/AgCl electrodes were placed in each side of the conductivity cell to measure a 18
transmembrane potential across the membrane. The transmembrane potential was varied from 19
-1V to 1V. 20
2.6 Procedure for sensing aptamer 21
ATP binding aptamer of different concentration was initially added on the tip side of the 22
conical nanopore. A 5 min voltage scan from -1V to 1V was employed to facilitate 1
accumulation of probe onto the surface of the conical nanopore. 2
2.7 Procedure for sensing the aptamer-ATP complexes 3
Different concentrations of ATP from 50 nM to 10 μM were mixed with 1 μM binding 4
aptamer (200 μL) in the centrifuge tube for 2 h. And then, 500 μg/mL single-walled carbon 5
nanotubes (100 μL) was added to the centrifuge tube and wait for another 30 min (Guo et al. 6
2012). The resulting solution was diluted to 1 mL with Tris-HCl buffer. After that, the mixture 7
was placed on the tip side of the conical nanopore and detected as described above. 8
2.8 Cellular ATP assay 9
The Hela cell was cultured in RPMI-1640 medium supplemented with 10% fetal bovine 10
serum (FBS) at 37 oC and in a humidified air contained 5% CO2. The trypsin was added to the 11
cell solution and the digestion was conducted for 4 min. The cell was collected after trypsin 12
digestion, then washed by Tris-HCl buffer three times and suspended in the Tris-HCl buffer 13
again. Cell lysis (approximately 200,000 cells/mL) was obtained by three times of 14
freeze-thaw cycles. Then the solution was used in the detection of ATP. 15
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3. Results and discussion 17
Ion current rectification is one of the intriguing characteristics for single conical nanopore 18
with charged surface, which attracts increasing attention in recent years. The mechanism of 19
the current rectification has been sufficiently investigated by Z siwy. In 2008, Wang had first 20
employed this phenomenon to prepare a nanopore sensor to detect hydrophobic drug. 21
Afterwards, a lot of nanopore sensors were constructed and widely applied in the detection of 22
analyte. Relative to the bare nanopore without modifications in early research, more and more 1
studies concentrated on grafting functional groups on the surface of the nanopore to provide 2
recognition sites for analytes. In this study, we applied asymmetric nanopore sensor coated 3
with zirconium ion, using PEI as adhesive layer, to count ATP-aptamer complex for indirect 4
detection of ATP. 5
3.1. Characterization of chemically-modified nanopore 6
The whole fabrication and modification process can be easily monitored via ion-current 7
rectification (Figure 1). A nascent nanopore after chemical etching presents abundant 8
carboxyl groups on the nanopore surface and the corresponding ion-current rectification 9
shows a nonlinear curve in the downward shape (Figure 1, black curve). The nonlinear shape 10
can be fully reversed into an upward shape after absorption of PEI polymer in 1% (w/v) 11
aqueous solution for 5 h, indicating the positively-charged status of the nanopore ( Figure 1, 12
red curve). Electrostatic interaction between the negative charge on the nanopore surface and 13
the positive charge on the PEI polymer plays a very important role in the adsorption of PEI 14
onto the nanopore surface. Zr4+
was confirmed to be easily adsorbed onto the amino-rich PEI 15
polymer by the ion current rectification (Figure 1, blue curve). Until now, few studies have 16
investigated the interaction between Zr4+
and PEI, while other metal ions such as Cu2+
, Cd2+
, 17
Cr3+
and Pb2+
have been extensively studied in terms of the interaction with PEI (Chen et al. 18
2010; Fan et al. 2013; Gao et al. 2014; Liu and Huang 2011; McNeff and Carr 1995). 19
With only PEI coated, the nanopore shows negligible response to phosphate-rich DNA 20
polymer with 27 bases, which is clearly demonstrated in Figure 2A. It can be concluded that 21
the electrostatic interaction between short DNA and positively charged PEI is not strong 22
enough to allow the current change via the nanopore. In contrary to PEI-coated nanopore, the 1
nanopore coated with PEI/Zr4+
shows DNA concentration-dependent current responses 2
(Figure 2B). The strong interaction between Zr4+
and phosphoric group plays very important 3
roles, which has already been manifested in many studies (Shervedani and Pourbeyram 2010; 4
Wang et al. 2007a). For sensing purpose, the surface adsorption of free DNA is extremely 5
unfavorable for achievement of the sensor quality. In order to resolve this issue, SWNTs 6
which have been proved to bind single strand DNA are added into the DNA solution. Figure 7
2C clearly shows that the free DNA adsorption can be efficiently prevented. The ratio of 8
SWNTs to the ATP aptamer was systematically investigated (Figure S5). The 50 μg/mL 9
concentration of SWNTs was chosen in the presence of 200 nM aptamer. Finally, whether 10
free ATP as a biomolecule with phosphate groups could contaminate the nanopore surface 11
was investigated (Figure 2D), it obviously shows that the ATP concentrations up to 10 μM 12
only had negligible influence on the ion-current rectification. 13
Fig. 1 14
Fig. 2 15
3.3 Optimization of the SWNTs concentration 16
The ratio of the SWNTs concentration to aptamer is pretty important since improper 17
ratio could degrade the sensor’s sensitivity. The determination of proper ratio was achieved 18
via fluorescence titration. As shown in Fig. S5A (supporting information), with the increasing 19
concentration of the SWNTs, the fluorescence intensity of FAM-labelled DNA was gradually 20
decreased since the aptamer was adsorbed onto the surface of SWNTs. At a concentration of 21
50 μg/mL SWNTs, more than 95% FAM’s fluorescence was quenched. So 50 μg/mL SWNTs 22
was adopted in the presence of 200 nM aptamer for the subsequent experiments. All the 1
nanopore tests (Figure 2D) showed that this concentration was sufficient enough to eliminate 2
the interference of free aptamer. The detailed structure of SWNTs measured by Transmission 3
Electron Microscopy (TEM) is shown in Figure S3 (Supporting Information) 4
3.4 Confirmation of Zr4+
coating by XPS characterization 5
X-ray photoelectron spectroscopy (XPS) was used to characterize the surface chemistry of 6
the multi-tracked PET membranes. XPS data were obtained with an ESCALab250i-XL 7
electron spectrometer from VG Scientific using 300 W Al Kα radiations. Fig. S4A 8
(Supporting information) clearly shows a much higher value of the N1s peak in XPS spectra 9
for the PET membrane after PEI adsorption compared to the naked PET membrane. PEI 10
adsorption provided tons of anchoring points for the subsequent metal ion coating. Since a 11
number of literatures (Shervedani and Pourbeyram 2010; Wang et al. 2007a) have reported 12
that Zr4+
strongly binds DNA via electrostatic force, polyvalent Zr4+
was applied in our 13
experiments. The XPS spectra (Figure S4B) demonstrate that Zr4+
was successfully coated 14
onto the PEI adsorbed on track-etched membrane. The peaks corresponding to Zr (3d3/2 at 15
181.85 eV; 3d5/2 at 183.75 eV) are only observable in Figure S4B (b) after Zr4+
coating, 16
while there is no peaks for the PET surface without any modification as shown in Figure S4B 17
(a). 18
3.5 Quantitative Detection of ATP 19
The concentration of ATP determines the complex (ATP/aptamer) concentration, which 20
can be monitored by the I-Vcurve. With the fixation of aptamer and SWNTs concentration at 21
200 nM and 50 μg/L, respectively, the concentration of the complex (ATP/Aptamer) in 22
solution has linear relationship with the ATP concentration in solution. Therefore, the ATP 1
concentration can be indirectly quantitated by asymmetrical nanopore coated with PEI/Zr4+
. 2
The adsorption behavior of the complex (ATP/Aptamer) adheres to Langmuir absorption 3
model. The ATP concentration was indirectly monitored by the change of the I-Vcurve after 4
the adsorption of the complex onto the nanopore surface. According to the Langmuir model 5
reported previously (Wang and Martin 2008), the surface coverage (θ) is related with the ATP 6
concentration via the equation 1. 7
θ=KC/ (1+KC) (1) 8
Where θ is the fractional coverage of the molecule on the surface, K is the binding constant 9
and C is the concentration of the ATP. θ is also given by 10
θ=(I0- Ii)/( I0-Imin) (2) 11
Where I0 is the current through the nanopore in the absence of the ATP, Imin is the minimum 12
current after the nanopore surface is saturated by high concentrated ATP. And Ii is defined as 13
the corresponding ion current exposed to the solution which is the immediate concentration of 14
ATP. The surface coverage (θ) plotted as the function of ATP concentration shows linear 15
relationship with ATP concentration below 200 nM (Figure 3). The limit of detection (LOD) 16
is calculated to be 27.46 nM according to the equation LOD = 3N/S. 17
Scheme 1 18
Fig. 3 19
3.7 Selectivity of the nanopore sensor toward ATP 20
The selectivity tests of the biosensor were conducted by examining the nanopore 21
responses to the ATP over the analogues of ATP such as CTP, UTP, GTP. 1 μM concentration 22
for the ATP and analogues were chosen. Under the same experimental conditions, the I-V 1
curve was acquired (Figure 4A). It was manifested in Figure 4B that the rectification ratio in 2
presence of ATP was changed much larger than that in presence of CTP, UTP and GTP since 3
those three analogues could not interact with the aptamer. The results demonstrated the 4
remarkable selectivity of the biosensor for the ATP is attributed to the specific interaction 5
between ATP and aptamer. 6
Fig. 4 7
3.8 Analysis of ATP in Hela cell 8
In order to prove this method can be used in the real samples, the biosensor was employed 9
to detect ATP from hela cell. Since the freezing and thawing technique allowed the cellular 10
content to flow out after cellular membrane disruption, ATP measured by nanopore can be an 11
indication of the ATP content in the cancer cell. As shown in Figue 5A and 5B, ATP content 12
measured immediately after cell membrane disruption by freezing and thawing technique was 13
distinctly higher than that measured 24 hours later after cell membrane disruption. These 14
experimental results were consistent with many other studies reported previously (Zhang et al. 15
2010). Undoubtedly, this sensing platform possesses the ability to analyze the real sample. 16
Fig. 5 17
3.9 The regeneracy of the synthetic nanopore sensor 18
Reusability of synthetic nanopore is an very important criteria to evaluate the quality of the 19
sensor. Until now, the progress in this aspect is still in a very early stage. Herein we 20
challenged our nanopore sensor by regenerating the nanopore surface for several times. The 21
I-V curve in Figure S6A shows that short time etching with 2M NaOH for 5 minutes was 22
good enough to remove the aptamer from the surface. Recycling the nanopore sensor for up to 1
4 times has been implemented (Figure S6B). As we know, longer etching can enlarge the 2
nanopore size significantly, therefore, long-term recycling of nanopore sensor is not 3
recommended. 4
4. Conclusions 5
In this study, we developed a label-free nanopore biosensor for the detection of ATP in 6
conjunction with SWNTs. This simple method evades direct immobilization of probe 7
molecules onto the asymmetric nanopore surface, whereas both selectivity and sensitivity can 8
be warranted. The key point of this strategy lies in that any aptamer-binding target can be 9
quantitated by counting the DNA concentration via the Zr4+
-coated nanopore sensor and free 10
interfering DNAs can be drawn away by SWNTs. The detection limit of this nanopore sensor 11
for ATP is 27.46 nM. Although only detection of ATP is demonstrated in this study, this 12
scenario can be expanded to analyze other target since there are a lot of studies regarding the 13
interaction between aptamer and other molecules. In the future research, signal amplification 14
will be integrated into this system for further improvement of sensitivity and selectivity. 15
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Acknowledgements 17
This work was supported by National Natural Science Foundation of China (No. 21190040 18
and 21275137), Start Funding from Changchun Institute of Applied Chemistry (CAS) and 19
Supporting Funding for Creative Young Scientist (CAS). Thanks for GSI providing 20
track-etched membranes. 21
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Figure captions. 1
Scheme 1. Schematic of the biomimetic nanopore preparation and the detection of ATP. (a) A 2
cone-shaped nanopore with abundant carboxyl groups on the surface. (b) Electrostatic 3
adsorption of PEI onto the nanopore. (c) Adsorption of Zr4+
onto the PEI-coated nanopore. (d) 4
Detection of aptamer-ATP complexes via the nanopore. The SWNTs remove the excess 5
ssDNA. 6
Fig. 1. I-V curve characterization of each preparation step of the biomimetic nanopore (tip 7
diameter = 92 nm, base diameter = 1100 nm). Nascent nanopore with abundant carboxyl 8
groups (black square), nanopore coated with PEI (red circle), nanopore coated with PEI/Zr4+
9
(blue triangle). 10
Fig. 2. (A) The responses of PEI-coated asymmetric nanopore (tip diameter = 92 nm, base 11
diameter = 1100 nm) to various concentrations of aptamer. (B) The responses of 12
PEI/Zr4+
-coated asymmetric nanopore (tip diameter = 74 nm, base diameter = 1100 nm) to 13
various concentrations of aptamer. (C) The responses of PEI/Zr4+
-coated asymmetric 14
nanopore (tip diameter = 78 nm, base diameter = 1100 nm) to 200 nM aptamer in the presence 15
of 50 μg/mL SWNTs. (D) The responses of PEI/Zr4+
-coated asymmetric nanopore (tip 16
diameter = 78 nm, base diameter = 1100 nm) to various concentrations of ATP. 17
Fig. 3. (A) The ATP concentration-dependent responses of PEI/Zr4+
-coated asymmetric 18
nanopore (tip diameter = 78 nm, base diameter = 1100 nm) in the presence of 200 nM 19
aptamer and 50 μg/mL SWNTs. (B) Plot of surface coverage (θ) versus ATP concentration. 20
Red line is the fitting curve based on langmuir model. The inset displays the linear response 21
for ATP concentration ranging from 0 nM to 200 nM. 22
Fig. 4. Selectivity of PEI/Zr4+
-coated asymmetric nanopore (tip diameter = 78 nm, base 1
diameter = 1100 nm) toward ATP against other ATP analogue. (A) The responses of 2
asymmetric nanopore sensor to UTP (1 μM), GTP (1 μM), CTP (1 μM) and ATP (1 μM), 3
respectively, in the presence of 200 nM aptamer and 50 μg/mL SWNTs. (B) The 4
corresponding columns whose values are the relative ratio of current change measured at +1 5
V. 6
Fig. 5. (A)The response of asymmetric nanopore sensor (tip diameter = 82 nm, base diameter 7
= 1100 nm) to ATP in Hela cell. (a) Only buffer solution, (b) buffering solution plus 200 nM 8
aptamer and 50 μg/mL SWNTs, (c) in the presence of lysed cells after 24-h aging (ATP absent) 9
under otherwise same conditions as (b), (d) in the presence of freshly lysed cells (ATP present) 10
under otherwise same conditions as (b). (B) The corresponding columns whose values are the 11
relative ratio of current change measured at +1 V. 12
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TOC 1
Without the interference from free target-specific probes that can be eliminated by SWNTs, 2
PET/Zr4+
coated nanopore that is responsive to the ATP-bound aptamer can quantitatively 3
detect ATP concentration. In contrast to previous studies based on nanopore, this study evades 4
the immobilization of target-specific probe onto the nanopore surface. 5
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